Cell analyzer and sorting method therefor

ABSTRACT

A cell analyzer and a sorting method for the cell analyzer are disclosed. Multiple optical signals generated by each of particles irradiated with light in a blood sample in a detection region are collected. The particles includes a first category of particles and a second category of particles. For each of the particles, Intensities of a first group of optical signals, which includes at least two optical signals selected from the multiple optical signals, and a pulse width of a second group of optical signals, which includes at least one optical signal selected from the multiple optical signals are acquired. For each of the particles, one or more reinforcement signals related to the particle are calculated based on an intensity of a first optical signal selected from the first group of optical signals and a pulse width of a second optical signal selected from the second group of optical signals, where the first optical signal is as same as or different from the second optical signal. The first category of particles and the second category of particles are distinguished from each other based at least partially on the one or more reinforcement signals related to each of the particles.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.16/414,023, filed on May 16, 2019, which is a continuation of U.S.patent application Ser. No. 15/675,079, filed on Aug. 11, 2017, for“Cell Analyzer and Particle Soring Method and Device,” which is acontinuation of PCT App. No. PCT/CN2015/072907, filed on Feb. 12, 2015,for “Cell Analyzer and Particle Sorting Method and Device,” each ofwhich are incorporated herein by reference.

TECHNICAL FIELD

The present disclosure relates to a medical devices, and moreparticularly to a cell analyzer and sorting method for the cellanalyzer.

BACKGROUND

A blood cell analyzer is an instrument that detects cells in the blood.It counts and sorts cells such as leucocytes (white blood cells or WBC),red blood cells, blood platelets, nucleated red blood cells andreticulocytes.

The most common cell analyzer used by a blood cell analyzer to detectleucocytes is a laser scattering cell analyzer, in which, by irradiatingcell particles flowing through a detection region with light, opticalsignals reflected or scattered by various categories of particles arecollected, and then the optical signals are processed and analyzed so asto sort and count the leucocytes. The collected optical signals mayinclude three types of optical signals, including forward-scatteredlight, side-scattered light, and fluorescence signals. Theforward-scattered light can reflect size information of the cell, theside-scattered light can reflect complexity of an internal structure ofthe cell, and the fluorescence signal reflects components in the cellthat can be dyed by a fluorescent dye, such as DNA and RNA. By means ofthese optical signals, the leucocytes can be sorted, and the leucocytecount can be obtained at the same time.

According to different pretreatments of blood samples (e.g., reagentsbeing different), detection processes are divided into differentdetection channels, such as a differential (DIFF) channel, a basophil(BASO) channel and a nucleated red blood cell (NRBC) channel. The BASOchannel is used to sort and count leucocytes, while a blood sample istreated with a chemical reagent, the total number of leucocytes iscounted by means of side-scattered light and forward-scattered light,and a count of basophil granulocytes in the leucocytes is also provided.The NRBC channel can be used to sort nucleated red blood cells after ablood sample is treated with a fluorescent reagent added therein. TheNRBC channel can provide a leucocyte count and a nucleated red bloodcell count.

During blood cell detection by a blood cell analyzer, two types ofparticles cannot be clearly distinguished from each other in some cases,thus affecting particle sorting results. For example, when countingleucocytes, the leucocytes may not be counted accurately due to theinfluence of interfering particles. The interfering particles mayinclude lipid granules or aggregated PLT (blood platelet) particles. PLTis a part of a blood ghost which is a cell debris structure formed aftera sample pretreatment of a blood sample, in which cells such as redblood cells or platelets are subjected to a hypotonic treatment ortreated with a reagent, resulting in cell membrane rupture. Generally,the particle size is small, and the forward-scattered light signal isweak. However, in some samples, PLT aggregation may occur andinterfering with the leucocyte detection. These interfering particlesmay overlap with the leucocyte in the scatter diagram. FIG. 1 shows adetection result of the NRBC channel, where an aggregated plateletcluster A1 overlaps with a leucocyte cluster B1 in the forward-scatteredlight and fluorescence signals. FIG. 2 shows a detection result of theBASO channel, where leucocytes are sorted into a basophil granulocytecluster A2 and a cluster B2 of other leucocyte particles includinglymphocytes, monocytes, neutrophil granulocytes and eosinophilgranulocytes. Due to the existence of lipid particles, a lipid granulecluster C2 overlaps with the cluster B2 of other leucocyte particles ina region D2 at a lower end of the forward-scattered light andside-scattered light signals, which may interfere with counting ofleucocytes. It can be seen that the existence of these interferingparticles in the blood sample will affect the accuracy of the detectionresults.

BRIEF SUMMARY

According to a first aspect, a sorting method for a cell analyzer isprovided. The method includes actions of collecting multiple opticalsignals generated by each of particles irradiated with light in a bloodsample in a detection region, the particles comprising a first categoryof particles and a second category of particles; for each of theparticles, acquiring intensities of a first group of optical signals,which comprise at least two optical signals selected from the multipleoptical signals, and a pulse width of a second group of optical signals,which comprises at least one optical signal selected from the multipleoptical signals; for each of the particles, calculating one or morereinforcement signals related to the particle, based on an intensity ofa first optical signal selected from the first group of optical signalsand a pulse width of a second optical signal selected from the secondgroup of optical signals, wherein the first optical signal is as same asor different from the second optical signal; and distinguishing betweenthe first category of particles and the second category of particlesbased at least partially on the one or more reinforcement signalsrelated to each of the particles.

According to a second aspect, a cell analyzer is provided. The cellanalyzer includes a reaction chamber, a flow chamber, a conveyingapparatus, an optical detection apparatus, and a data processingapparatus. The reaction chamber provides a location for reaction betweena blood sample and a reagent to get a sample liquid. The flow chamberhas a detection region, through which the sample liquid pass in sequencewith shrouding by a sheath liquid. The conveying apparatus has aconveying line and a control valve, wherein the sample liquid isconveyed into the flow chamber through the conveying line. The opticaldetection apparatus has a plurality of optical signal detectors,operable to collect multiple optical signals generated by each ofparticles irradiated with light in a blood sample in a detection region,the particles comprising a first category of particles and a secondcategory of particles. The data processing apparatus is configured to,for each of the particles, acquire intensities of a first group ofoptical signals, which comprise at least two optical signals selectedfrom the multiple optical signals, and a pulse width of a second groupof optical signals, which comprises at least one optical signal selectedfrom the multiple optical signals; for each of the particles, calculateone or more reinforcement signals related to the particle, eachreinforcement signal comprising a reinforcement signal based on anintensity of a first optical signal selected from the first group ofoptical signals and a pulse width of a second optical signal selectedfrom the second group of optical signals, wherein the first opticalsignal is as same as or different from the second optical signal; anddistinguish between the first category of particles and the secondcategory of particles based at least partially on the one or morereinforcement signals.

According to a third aspect, a sorting method for a cell analyzer isprovided. The method includes actions of collecting multiple opticalsignals generated by each of particles irradiated with light in a bloodsample in a detection region, the particles comprising a first categoryof particles and a second category of particles, and the multipleoptical signals comprising a forward-scattered light signal and aside-scattered light signal; for each of the particles, acquiringintensities of the forward-scattered light signal and the side-scatteredlight signal, and a pulse width the forward-scattered light signal; foreach of the particles, calculating a reinforcement signal related to theparticle, based on the intensity of the forward-scattered light signaland the pulse width of the forward-scattered light signal; generating afirst scatter diagram for the particles based on the reinforcementsignal related to each of the particles and the intensity of theside-scattered light signal of the respective particle; anddistinguishing between the first category of particles and the secondcategory of particles based on the first scatter diagram, wherein thefirst category of particles are leucocyte particles, and the secondcategory of particles are lipid granules.

According to a fourth aspect, a sorting method for a cell analyzer isprovided. The method includes actions of collecting multiple opticalsignals generated by each of particles irradiated with light in a bloodsample in a detection region, the particles comprising a first categoryof particles and a second category of particles, and the multipleoptical signals comprising a fluorescence signal and at least onescattered light signal; for each of the particles, acquiring intensitiesof a first optical signal and a second optical signal selected from themultiple optical signals and a pulse width of a third optical signalselected from the multiple optical signals, the first optical signalbeing different from the second optical signal, and the third opticalsignal being as same as or different from the first optical signal orthe second optical signal; for each of the particles, calculating areinforcement signal related to the particle, based on the intensity ofthe first optical signal and the pulse width of the third light signal;generating a first scatter diagram for the particles based on thereinforcement signal and the intensity of the second optical signal ofeach of the particles; and distinguishing between the first category ofparticles and the second category of particles based on the firstscatter diagram.

According to a fifth aspect, a non-transitory computer readable storagemedium is provided, in which instructions are stored. The instructions,when executed by a processor, cause the processor to execute the methodaccording to the first aspect.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is an NRBC channel scatter diagram of a blood plateletaggregation sample;

FIG. 2 is a BASO channel scatter diagram of a lipid granule sample;

FIG. 3 is a schematic diagram of a detected pulse;

FIG. 4a is a forward-scattered pulse width-forward-scattered lightscatter diagram of the lipid granule sample;

FIG. 4b is a forward-scattered pulse width-side-scattered light scatterdiagram of the lipid granule sample;

FIG. 5 is a structural schematic diagram of a blood cell analyzer;

FIG. 6 is a structural schematic diagram of a particle sorting device;

FIG. 7 is a structural schematic diagram of a particle sorting device;

FIG. 8 is an NRBC channel scatter diagram of a normal sample;

FIG. 9 is a flow diagram of NRBC channel particle sorting;

FIG. 10 is an NRBC channel scatter diagram with the fluorescence signalreinforced by the forward-scattered pulse width;

FIG. 11 is an NRBC channel scatter diagram with the forward-scatteredlight signal reinforced by the forward-scattered pulse width;

FIG. 12 is an NRBC channel scatter diagram with the fluorescence signalreinforced by the side-scattered pulse width;

FIG. 13 is an NRBC channel scatter diagram with the forward-scatteredlight signal reinforced by the side-scattered pulse width;

FIG. 14 is an NRBC channel scatter diagram with the fluorescence signalreinforced by the fluorescence pulse width;

FIG. 15 is an NRBC channel scatter diagram with the forward-scatteredlight signal reinforced by the fluorescence pulse width;

FIG. 16 is a BASO channel scatter diagram of the normal sample;

FIG. 17 is a flow diagram of BASO channel particle sorting;

FIG. 18 is a BASO channel scatter diagram with the forward-scatteredlight signal reinforced by the forward-scattered pulse width;

FIG. 19 is a BASO channel scatter diagram with the forward-scatteredlight signal reinforced by the square of the forward-scattered pulsewidth;

FIG. 20A is a scatter diagram with the forward-scattered light signaland the side-scattered light signal showing four-classification of theleucocytes; and

FIG. 20B is a scatter diagram with the forward-scattered light signaland the medium-angle-scattered light signal showing four-classificationof the leucocytes.

DETAILED DESCRIPTION

A particle passing through a detection region generates a pulse, and thewidth of the pulse (hereinafter referred to as pulse width) can reflectthe time during which the particle passes through the detection region,and thus can characterize the size of the particle. FIG. 3 shows aschematic diagram of a detected pulse, where a pulse signal is excitedwhen a particle passes through a detection region. The pulse width isfrom the start of the pulse to the end of the pulse, and the pulse widthsignal is the time during which the particle passes through thedetection region. When the flow rate is constant, the smaller theparticle is, the shorter the time will be during which the particlepasses through the detection region is, and in turn the smaller thecorresponding pulse width will be. By contrast, the larger the particleis, the longer the time during which the particle passes through thedetection region, and in turn the greater the corresponding pulse widthwill be. Therefore, it is theoretically possible to distinguish betweendifferent kinds of particles by pulse width.

In a sample where platelet aggregation occurs, the width of a pulsegenerated by aggregated particles when passing through the detectionregion is relatively large. It is theoretically possible to distinguishbetween aggregated blood platelet particles and leucocytes by pulsewidth. However, due to the fact that the number of blood plateletsaggregated together is different, the blood platelet clusters rangewidely in particle size, some aggregated blood platelet particles of alarger size will overlap with leucocyte groups. Therefore, theleucocytes and the aggregated blood platelet particles cannot beperfectly distinguished from each other by pulse width.

With regard to lipid granules in a blood sample, because the sizethereof varies, the volume thereof presents a variation from small tolarge magnitudes in each case. For lipid granule particles of smalldiameters, the corresponding pulse width is small; and for lipid granuleparticles of large diameters, the corresponding pulse width is large. Inthe case of a small pulse width, it is possible that the pulse width ofa lipid granule is equal to that of a leucocyte. As shown in FIGS. 4Aand 4B, it can be seen that a lipid granule cluster A4 has from small tolarge pulse widths, and overlaps with a basophil granulocyte cluster B4and a cluster C4 of other leucocyte particles in the small pulse widthpart. Consequently, the lipid granules and the leucocytes cannot beseparated from each other favorably according to pulse width, whetherbased on a forward-scattered light scatter diagram or on aside-scattered light scatter diagram.

Therefore, in embodiments of the present disclosure, according to thedifference in pulse width between the interfering particles and theleucocyte particles, a new reinforcement signal is formed by combining afunction of an optical signal with a function of the pulse width signal,so that a scatter diagram generated based on the reinforcement signalcan significantly enhance the effect of separating particle groups.

In the present disclosure, a new reinforcement signal is formed bycombining a function of a certain optical signal and a function of apulse width signal so that the difference between the first category ofparticles and the second category of particles in the reinforcementsignal is increased, and a new scatter diagram is generated based on thereinforcement signal. By means of the greater difference between thefirst category of particles and the second category of particles in thereinforcement signal, the first category of particles and the secondcategory of particles can be distinguished from each other, therebyimproving the accuracy of particle sorting.

As those skilled in the art would understand, the scatter diagram ismerely a data representation form. The scatter diagrams in the presentdisclosure are not limited to the graphic presentation form. Forexample, the scatter diagram may be in a data form. In some embodimentsof the disclosure, no scatter diagram is generated. Instead, the firstcategory of particles and the second category of particles can bedistinguished from each other based on the reinforcement signal by usingother data analysis approaches.

FIG. 5 shows a structural schematic diagram of a blood cell analyzer.The blood cell analyzer comprises an optical detection apparatus 20, aconveying apparatus 30, a data processing device 40 and a displayapparatus 50.

The conveying apparatus 30 conveys a sample liquid (e.g., a blood sampleto be tested) after reaction with a reagent to the optical detectionapparatus 20. The conveying apparatus 30 typically comprises a conveyingline and a control valve, where the sample liquid is conveyed into theoptical detection apparatus 20 through the conveying line and thecontrol valve.

The optical detection apparatus 20 irradiates the sample liquid flowingthrough the detection region thereof with light, collecting variousoptical information (e.g., scattered light information and/orfluorescence information) generated by cells irradiated with light, andconverting the optical information into corresponding electric signals.The information corresponds to the characteristics of the cell particlesand can be used as characteristic data of the cell particles. Theforward-scattered light signal reflects size information of the cell,the side-scattered light signal reflects complexity of an internalstructure of the cell, and the fluorescence signal reflects thecomponent in the cell that can be dyed by a fluorescent dye, such as DNAand RNA. In the embodiment shown in FIG. 5, the optical detectionapparatus 20 can include a light source 1025, a detection region 1021serving as the detection region, a forward-scattered light signalcollecting device 1023 provided on an optical axis, a side-scatteredlight signal collecting device 1026 and a fluorescence signal collectingdevice 1027 provided at a side of the optical axis. In some embodiments,the fluorescence signal collecting device 1027 is not required. Instead,the fluorescent signal collecting device 1027 includes aforward-scattered light collecting device 1023, a side-scattered lightcollecting device, and a medium-angle-scattered light collecting devicefor collecting a medium-angle-scattered light signal at an angle betweenthe forward-scattered light (FS) and the side-scattered light(SS), whichmay be a low-medium-angle-scattered light signal at an angle of about 8°to about 24° to the incident beam, or a high-medium-angle-scatteredlight signal at an angle of about 25° to the incident beam. In FIG. 20Aand FIG. 20B, a comparison is performed between classification ofleucocyte particles based on the forward-scattered light signal(FS)—side-scattered light signal (SS) scatter diagram, andclassification of leucocyte particles based on the forward-scatteredlight signal (FS)—high-medium-angle-scattered light signal (MS). Theclassifications of the leucocyte particles on the scatter diagrams showthat both can distinguish leucocyte particles into four categories. Itindicates that the medium-angle-scattered light signal can be used as acombined signal, or a pulse signal of the medium-angle-scattered lightsignal can be used in combination with a combined signal to calculate areinforcement signal, or the medium-angle-scattered light signal can beused in combination with a reinforcement signal to generate a newscatter diagram.

A blood sample is separated as needed. A part of the blood sample reactswith a reagent in a reaction chamber (not shown) to get a sample liquid.Particles in the sample liquid pass through the detection region 1021 ofa flow chamber 1022 in sequence with shrouding by a sheath liquid. Alight beam emitted by the light source 1025 is projected to thedetection region 1021. Cell particles in the sample liquid areirradiated with the light beam and then emit scattered light. The lightcollecting device collects the scattered light, and the collected andshaped light is projected to a photoelectric sensor. The photoelectricsensor converts the optical signal into a corresponding electricalsignal and outputs the electrical signal to the data processing device40.

The data processing device 40 is configured to receive opticalinformation output from the optical detection apparatus 20, where theoptical information of each particle is used as a characteristic dataset characterizing the particle, and an analysis of the blood sample isrealized by analyzing and processing the characteristic data of theparticles. In one embodiment, the data processing device 40 includes aparticle sorting device that generates a desired scatter diagram basedon the characteristic data sets of the particles and sorts the particlesaccording to the scatter diagram. In some embodiments, the particlesorting device distinguishes leucocytes from interfering particles,where the interfering particles may be aggregated blood plateletparticles or lipid granules. In some embodiments, the scatter diagramrefers to a set of characteristic data sets of the cell particles, whichmay be stored in a storage device in a digitized form, or may bepresented in a visualized form on a display interface.

The display apparatus 50 is electrically coupled to the data processingdevice 40 to display the analysis result output by the data processingdevice 40, and the analysis result may be a graphic, a text description,a table, and/or the like. In one embodiment, the display apparatus 50may output various visualized scatter diagrams and/or various cellsorting results.

In one embodiment, leucocyte particles and interfering particles aredistinguished from each other by means of reinforcement signals ofoptical signals and pulse width signals, regardless of the presence orabsence of the interfering particles and whether or not the interferingparticles overlap with the leucocytes. As shown in FIG. 6, a particlesorting device includes an optical signal acquisition unit 41, a pulsewidth acquisition unit 42, a calculating unit 43, a new scatter diagramgenerating unit 44 and a sorting unit 45. These and the other unitsdescribed herein may be implemented using any combination of hardware,software, and/or firmware.

The optical signal acquisition unit 41 acquires an optical signal. Whenthe blood sample passes through a detection region, the detection regionis irradiated with light emitted by the optical detection apparatus 20,and particles in the sample are irradiated with the light to generatecorresponding optical signals. The optical detection apparatus 20collects various optical information generated by the particles due tothe light irradiation. The optical signals include at least two offorward-scattered light, side-scattered light and fluorescence, forexample, forward-scattered light and side-scattered light, or theforward-scattered light, the—side scattered light and the fluorescence.

The pulse width acquisition unit 42 acquires a pulse width of at leastone optical signal. In some embodiment, the pulse width acquisition unit42 selects an optical signal from the collected optical signals andrecords the pulse width of this optical signal, for example, it canrecord the pulse width of the forward-scattered light, theside-scattered light or the fluorescence. In another particularembodiment, the pulse width acquisition unit 42 selects a plurality ofoptical signals from the collected optical signals and records the pulsewidth of each of the plurality of optical signals, for example, thepulse widths of both the forward-scattered light and the fluorescence.

The calculating unit 43 calculates a reinforcement signal. Thereinforcement signal is calculated from the pulse width of an opticalsignal and a combined optical signal using a combinatorial function. Thecombined optical signal may be any one of the optical signals obtainedby the optical signal acquisition unit 41. The combinatorial calculationincreases the difference in the reinforcement signal between theleucocyte particles and the interfering particles relative to thedifference between the two in the combined optical signal. For example,the reinforcement signal may be a function of the combined opticalsignal and the pulse width, which has an expression as follows:Z=f(X,Y)  (1)

where Z is the reinforcement signal; f is the function; X is theintensity of the combined optical signal, where in some embodiments, theintensity of an optical signal can be the peak value of the opticalpulse signal; and Y is the pulse width.

According to expression (1) above, the function f has the followingcharacteristics:

the function f is monotonic for the combined optical signal or pulsewidth, i.e., when the combined optical signal is fixed (or constant),the function is a monotonic function for the pulse width, for example,the function is an increasing or decreasing function of the pulse width;and when the pulse width is fixed, the function is a monotonic functionfor the combined optical signal, for example, the function is anincreasing or decreasing function of the combined optical signal.

Alternatively, the function f has the following characteristics: thefunction f is a non-linear combinatorial function of the combinedoptical signal and the pulse width.

In some embodiments, the reinforcement signal obtained through thecombinatorial calculation by the calculating unit 43 may comprise onesignal, for example, the reinforcement signal is only a reinforcementsignal of the forward-scattered light with the pulse width. Thereinforcement signal obtained through combinatorial calculation by thecalculating unit 43 may comprise a plurality of types of signals. Forexample, the reinforcement signal may be a reinforcement signal of theforward-scattered light with the pulse width, combined with areinforcement signal of the side-scattered light with the pulse width.In some embodiments, the optical signal of which the pulse width isrecorded and the combined optical signal may be the same optical signalor may be different optical signals.

The new scatter diagram generating unit 44 forms a new scatter diagramon the basis of the reinforcement signal and at least another signal,and the at least another signal may be at least one optical signaldifferent from the combined optical signal, or at least one of or acombination of two other reinforcement signals. The new scatter diagrammay be two-dimensional or three-dimensional, where at least onedimension is the reinforcement signal.

In some embodiments, a new scatter diagram is formed by selecting anoptical signal and a reinforcement signal, for example, selecting oneoptical signal and one reinforcement signal to form a two-dimensionalnew scatter diagram, or selecting one optical signal and tworeinforcement signals to form a three-dimensional new scatter diagram,or selecting two optical signals and one reinforcement signal to form athree-dimensional new scatter diagram.

In some implementations, an optical signal may be selected that isdifferent from the combined optical signal and a reinforcement signal toform a new scatter diagram. For example, if the combined optical signalfor calculating the reinforcement signal is fluorescence, theforward-scattered light and the reinforcement signal are selected toform a new scatter diagram.

In another particular embodiment, a certain reinforcement signal andother reinforcement signals are selected to form a new scatter diagram,where the other reinforcement signals refer to a reinforcement signaldifferent from the certain reinforcement signal, for example, selectingan A-type reinforcement signal from the at least one reinforcementsignal calculated by the calculating unit 43 as a dimension of the newscatter diagram, and then selecting a B-type reinforcement signaldifferent from the A-type reinforcement signal as another dimension ofthe new scatter diagram. In other words, the new scatter diagram selectstwo types of reinforcement signals to form a two-dimensional new scatterdiagram, e.g., selecting a reinforcement signal of the forward-scatteredlight and the pulse width, and a reinforcement signal of theside-scattered light and the pulse width to form a two-dimensional newscatter diagram.

The sorting unit 45 distinguishes between the leucocyte particles andthe interfering particles according to the new scatter diagram.Leucocyte particles and interfering particles differ slightly in opticalsignal and pulse width, but the difference is not sufficient todistinguish between the leucocyte particles and the interferingparticles. The difference can be increased by a combinatorialcalculation of the optical signals and the pulse width. Since thereinforcement signal increases the difference in the reinforcementsignal between the leucocyte particles and the interfering particlesrelative to the difference between the two in the combined opticalsignal, the leucocyte particles and the interfering particles can bedistinguished from each other in a scatter diagram based at least on thereinforcement signal.

In another embodiment, a conventional cell analyzer is used first, i.e.,a scatter diagram is generated based on an optical signal, which isreferred to as an initial scatter diagram. When there is an overlapregion in the initial scatter diagram between leucocyte particles andinterfering particles, a reinforcement signal of the optical signal andthe pulse width signal are used then to distinguish between theleucocyte particles and the interfering particles.

As shown in FIG. 7, a particle sorting device includes an optical signalacquisition unit 51, an initial scatter diagram generating unit 52, apulse width acquisition unit 53, a calculating unit 54, a new scatterdiagram generating unit 55 and a sorting unit 56. The optical signalacquisition unit 51, the calculating unit 54 and the new scatter diagramgenerating unit 55 may be the same as those in the foregoing embodiment.The initial scatter diagram generating unit 52 generates an initialscatter diagram for sorting and/or counting the leucocytes according toan optical signal. The pulse width acquisition unit 53 acquires a pulsewidth of at least one optical signal when there is an overlap regionbetween a leucocyte particle cluster and an interfering particle clusterin the initial scatter diagram. The sorting unit 56 distinguishesbetween the leucocyte particles and the interfering particles andcounting the leucocytes according to the new scatter diagram. When theleucocyte particle cluster and the interfering particle cluster have nooverlap regions in the initial scatter diagram, the sorting unit 56 alsocounts the leucocytes according to the initial scatter diagram.

The following disclosure relates to embodiments of specific bloodsamples.

In one embodiment, a blood platelet aggregation sample is taken as anexample, the blood sample was measured by a blood cell analyzer, and aleucocyte count can be obtained through an NRBC channel.

In general, red blood cells and blood platelets will form cell debrisafter being treated with a hemolytic agent, and the cell debris will belocated in a part of lower-end signals in the NRBC channel aftermeasurement by the blood cell analyzer. A NRBC channel scatter diagramof a normal sample is shown in FIG. 8. It can be seen that the bloodghost A5 and leucocyte cluster B5 are significantly separated from eachother, so that the blood ghost will not interfere with the leucocytecounting.

When there is blood platelet aggregation in a blood sample, thehemolytic agent cannot dissolve the blood platelet favorably, so thataggregated blood platelets may remain in the blood sample, and theaggregated blood platelets have a high signal intensity and will overlapwith a leucocyte group. As shown in FIG. 1, aggregated blood plateletparticle group A1 and leucocyte group B1 overlap with each other,affecting the leucocyte counting through the NRBC channel.

A processing method is shown in FIG. 9 In block 61, optical signalsgenerated by particles irradiated with light in a blood sample areacquired when the sample passes through a detection region, the opticalsignals including forward-scattered light, side-scattered light andfluorescence. In one embodiment, the fluorescence is side fluorescence.

In block 62, a pulse width of the forward-scattered light is recorded(hereinafter referred to as forward-scattered pulse width).

In block 63, the reinforcement signal is calculated based on the pulsewidth. The fluorescence signal is selected as a combined optical signal,and the reinforcement signal is the product of a fluorescence signalincreasing function and a pulse width increasing function, with aformula as follows:Z1=fx·fy  (2)

where Z1 is a fluorescence—forward-scattered pulse width reinforcementsignal, fx is an increasing function of the intensity of thefluorescence signal, and fy is an increasing function of theforward-scattered pulse width.

In some embodiments, the signal intensity of the fluorescence signal ismultiplied by the forward-scattered pulse width to obtain afluorescence—forward-scattered pulse width reinforcement signal.

In block 64, the forward-scattered light and thefluorescence—forward-scattered pulse width reinforcement signal areselected to form a new scatter diagram. As shown in FIG. 10, theabscissa is the fluorescence—forward-scattered pulse width reinforcementsignal, the ordinate is the forward-scattered light, A1 is theaggregated blood platelet particle group, and B1 is the leucocyteparticle cluster.

In block 65, the particles are sorted and/or counted according to thenew scatter diagram. In one embodiment, the leucocyte particles and theinterfering particles are distinguished from each other according to thenew scatter diagram. Typically, in the overlap region, the pulse widthof the platelets tends to be greater than the pulse width of theleucocyte particles. According to FIG. 1, the aggregated blood plateletparticle group A1 is located on the lower right side of the leucocyteparticle cluster B1. In the direction of the fluorescence, where theforward-scattered light is the same, the fluorescence intensity of theblood platelet particles is greater than the fluorescence intensity ofthe leucocyte particles, or the fluorescence intensity at the center ofthe aggregated blood platelet particle group A1 is greater than thefluorescence intensity at the center of the leucocyte particle clusterB1. After multiplying the fluorescence intensities of the bloodplatelets and the leucocyte particles respectively by the pulse width,as for the multiplication of the large factors, the product will be evenlarger, while for the multiplication of the small factors, the productwill be even smaller, the difference in the reinforcement signal betweenthe blood platelets and the leucocyte particles is greater, and isincreased relative to the difference in the fluorescence signal betweenthe two. As shown in FIG. 10, the aggregated blood platelet particlegroup A1 is shifted more to the right relative to the leucocyte particlecluster B1, so that the overlap region between the aggregated bloodplatelet particle group A1 and the leucocyte particle cluster B1 iseliminated. Therefore, the leucocyte particles and the blood plateletscan be distinguished from each other more easily and more accurately inthe new scatter diagram.

In block 63, the forward-scattered light may also be selected as acombined optical signal, and the reinforcement signal is a quotient of aforward-scattered light increasing function and a pulse width increasingfunction, for example, dividing the signal intensity of theforward-scattered light by the forward-scattered pulse width to obtain aforward-scattered—forward-scattered pulse width reinforcement signal. Inblock 64, the side-scattered fluorescence and theforward-scattere—forward-scattered pulse width reinforcement signal areselected to form a new scatter diagram, as shown in FIG. 11. Likewise,in the overlap region, the pulse width of the platelets is greater thanthe pulse width of the leucocyte particles. According to FIG. 1, in thedirection of the forward-scattered light, where the fluorescence is thesame, the forward-scattered light intensity of the blood plateletparticles is less than the forward-scattered light intensity of theleucocyte particles, or the forward-scattered light intensity at thecenter of the aggregated blood platelet particle group A1 is less thanthe forward-scattered light intensity at the center of the leucocyteparticle cluster B1. Moreover, the reinforcement signal is theforward-scattered light intensity divided by the forward-scattered pulsewidth, and therefore, in the new scatter diagram, the aggregated bloodplatelet particle group A1 will become smaller in the direction of thereinforcement signal, while the leucocyte particle cluster B1 willbecome greater in the direction of the reinforcement signal, so that thedifference between the leucocyte particles and the aggregated bloodplatelet particles is greater, and the leucocyte particles and theaggregated blood platelet particles can be distinguished from each othermore easily and more accurately.

That is to say, the calculation of the reinforcement signal may dependon the relative relationship between the first particle and the secondparticle in terms of the combined signal and the pulse width signal. Forexample, when the combined signals S and the pulse width signals W ofthe two particles A and B have the same magnitude relationship, theproduct is used; otherwise, the quotient is used. Specifically, if thecombined signals S meet the formula SA>SB, and the pulse width signals Wmeet the formula WA>WB, the reinforcement signal is calculated based onthe S*W, where the combined signal may be a fluorescence signal. If thecombined signals S meet the formula SA<SB and the pulse width signals Wmeet the formula WA>WB, the reinforcement signal is calculated based onS/W, where the combined signal may be forward scattered light. In oneexample, when determining the magnitude relationship between the firstparticle and the second particle in terms of the combined signal S andthe pulse width signal W, Δs*Δw can be adopted. Δs*Δw>0 indicates thatthe combined signals of the two particles have the same magnituderelationship as that of the pulse width signals of the two particles,and Δs*Δw<0 indicates that the combined signals of the two particleshave opposite magnitudes to that of the pulse width signals of the twoparticles. Δs represents the difference in statistical intensities ofthe combined signals of the two particles, Δw represents the differencein the statistical pulse widths of the pulse width signals of the twoparticles. In practice, quantitative calculations of Δs and Δw is notnecessary. As long as it is determined whether each of Δs and Δw isgreater than or less than zero, the manner of calculation of thereinforcement signal may be selected appropriately.

In other embodiment, the pulse width may also be the pulse width ofside-scattered light or fluorescence.

As shown in FIG. 12, the pulse width is the pulse width of theside-scattered light (referred to as side-scattered pulse width), andthe reinforcement signal is the product of the fluorescence and theside-scattered pulse width (referred to as fluorescence—side-scatteredpulse width reinforcement signal). The forward-scattered light and thefluorescence—side-scattered pulse width reinforcement signal areselected to form a new scatter diagram. According to the new scatterdiagram, the leucocyte particle cluster B1 and the aggregated bloodplatelet particle group A1 can also be distinguished from each othermore easily and accurately.

As shown in FIG. 13, the pulse width is the pulse width of theside-scattered light (referred to as side-scattered pulse width), andthe reinforcement signal is the quotient of the forward-scattered lightdivided by the side-scattered pulse width (referred to asforward-scattered—side-scattered pulse width reinforcement signal). Theforward-scattered light—side-scattered pulse width reinforcement signaland the fluorescence are selected to form a new scatter diagram.According to the new scatter diagram, the leucocyte particle cluster B1and the aggregated blood platelet particle group A1 can also bedistinguished from each other more easily and accurately.

As shown in FIG. 14, the pulse width is the pulse width of thefluorescence (referred to as fluorescence pulse width), and thereinforcement signal is the product of the fluorescence multiplied bythe fluorescence pulse width (referred to as fluorescence—fluorescencepulse width reinforcement signal). The forward-scattered light and thefluorescence—fluorescence pulse width reinforcement signal are selectedto form a new scatter diagram. According to the new scatter diagram, theleucocyte particle cluster B1 and the aggregated blood platelet particlegroup A1 can also be distinguished from each other more easily and moreaccurately.

Since the pulse signal can be regarded as an approximately triangularshape, and in one embodiment, the reinforcement signal is the product ofthe fluorescence multiplied by the fluorescence pulse width, thereinforcement signal can be considered to be twice the area of thefluorescent pulse signal. That is, when the combined optical signalintensity and the pulse width for calculating the reinforcement signalbelong to the same optical signal, the reinforcement signal may be thearea of or several times the area of the pulse signal of a certainlight, which may be regarded as a special case of the reinforcementsignal. In this case, it is to be understood by those skilled in the artthat even if the area of or several times the area of the optical pulsesignal are taken as the reinforcement signal, it should still beregarded as a combinatorial calculation of the signal intensity andpulse width of a combined optical signal. In addition, the area of theoptical pulse signal can be calculated by multiplying a pulse peak valueby the pulse width according to the area formula of a triangle, or byaccumulating or integrating the optical signal within the pulse width.

As shown in FIG. 15, the pulse width is the pulse width of thefluorescence (referred to as fluorescence pulse width), and thereinforcement signal is the quotient of the forward-scattered lightdivided by the fluorescence pulse width (referred to asforward-scattered—fluorescence pulse width reinforcement signal). Theforward-scattered light—fluorescence pulse width reinforcement signaland the fluorescence are selected to form a new scatter diagram.According to the new scatter diagram, the leucocyte particle cluster B1and the aggregated blood platelet particle group A1 can also bedistinguished from each other more easily and more accurately.

As those skilled in the art would understand, in this embodiment, theoptical signals in the NRBC detection are used. In the forward-scatteredlight signal-fluorescence signal scatter diagram, NRBC can bedistinguished from the leucocytes, and the NRBC count and the leucocytecount may be acquired respectively.

In another embodiment, a lipid granule sample is taken as an example.The blood sample was measured by a blood cell analyzer, and a leucocytecount is obtained through a BASO channel.

There is no lipid granules in a normal sample in the BASO channel, sothat the leucocyte count is accurate. A BASO channel scatter diagram ofa normal sample is shown in FIG. 16, where the abscissa is theside-scattered light signal, the ordinate is the forward-scattered lightsignal. B6 is leucocytes other than basophil granulocytes, namelylymphocytes, monocytes, neutrophil granulocytes and eosinophilgranulocytes, being a main leucocyte cluster. A6 is basophilgranulocytes; C6 is blood ghost, that is, fragments of red blood cellsand platelets after treatment with a hemolytic agent. As can be seenfrom FIG. 16, there is few blood ghost spots in the normal sample, andthe blood ghost are located below the main leucocyte cluster and greatlyseparated from the main leucocyte cluster, so that the leucocytecounting will not be interfered with.

When there are lipid granules in the blood sample, an S-shaped curvewill be formed in the BASO channel, as shown in FIG. 2, where theabscissa is the side-scattered light signal, and the ordinate is theforward-scattered light signal. B2 is leucocytes other than basophilgranulocytes, namely lymphocytes, monocytes, neutrophil granulocytes andeosinophil granulocytes, being a main leucocyte cluster. A2 is basophilgranulocytes; C2 is blood ghost, that is, fragments of red blood cellsand platelets after treatment with a hemolytic agent. In particular, atthe lower end of the side-scattered light signal and theforward-scattered light signal, the lipid granules overlap with theleucocyte group and affect the leucocyte counting. Consequently, theleucocytes and the lipid granules cannot be distinguished from eachother by the side-scattered light and forward-scattered light signals.

To reduce the influence of lipid granules on the leucocyte counting, aprocessing procedure of one embodiment is shown in FIG. 17 In block 71,optical signals generated by particles irradiated with light in a bloodsample are acquired when the sample passes through a detection regionfor detection, the optical signals including forward-scattered light andside-scattered light.

In block 72, an initial scatter diagram is generated according to theforward-scattered light and the side-scattered light, where the abscissais the side-scattered light, and the ordinate is the forward-scatteredlight.

In block 73, it is determined whether there is an overlap region betweenlipid granules and a leucocyte group in the initial scatter diagram. Ifthere is no overlap region between lipid granules and a leucocyte groupin the initial scatter diagram, as shown in FIG. 16, block 74 isperformed; and if there is an overlap region between lipid granules anda leucocyte group in the initial scatter diagram, as shown in FIG. 2,block 75 is performed.

In block 74, sorting and/or counting the leucocytes is performedaccording to the initial scatter diagram.

In block 75, a pulse width of the forward-scattered light is recorded(hereinafter referred to as forward-scattered pulse width).

In block 76, the reinforcement signal is calculated based on the pulsewidth. The forward-scattered light is selected as a combined opticalsignal; the reinforcement signal is the product of a forward-scatteredlight increasing function and a pulse width increasing function. In someembodiments, the intensity of the forward-scattered light signal ismultiplied by the forward-scattered pulse width to obtain aforward-scattered light—forward-scattered pulse width reinforcementsignal.

In block 77, the side-scattered light and the forward-scatteredlight—forward-scattered pulse width reinforcement signal are selected toform a new scatter diagram. As shown in FIG. 18, the abscissa is theside-scattered light, the ordinate is the forward-scatteredlight—forward-scattered pulse width reinforcement signal, A2 is abasophil granulocyte cluster, B2 is a main leucocyte cluster, and C2 islipid granules.

In block 78, the particles are sorted and/or counted according to thenew scatter diagram. In one embodiment, the leucocyte particles and theinterfering particles are distinguished from each other according to thenew scatter diagram. As shown in FIG. 2, in the region D2 where thelipid granules overlap with the leucocyte group, the lipid granules arelocated on the lower right side of the main leucocyte cluster B2. In thedirection of the forward-scattered light, where the side-scattered lightis the same, the forward-scattered light intensity of the lipid granulesis less than the forward-scattered light intensity of the leucocyteparticles. As shown in FIGS. 4A and 4B, at the lower end of theforward-scattered light signal, the pulse width of the lipid granules A4is smaller than the pulse width of the main leucocyte cluster C4.

After multiplying the forward-scattered light intensities of the lipidgranules and the leucocyte particles respectively by the pulse width, asfor the multiplication of the large factors, the product will be evenlarger, while for the multiplication of the small factors, the productwill be even smaller, the difference in the reinforcement signal betweenthe lipid granules and leucocyte particles is greater, and the distanceis increased relative to the difference in the forward-scattered lightsignal between the two. As shown in FIG. 18, the lipid granules C2 areshifted more to the lower right side relative to the main leucocytecluster B2, such that there is already an apparent empty space W betweenthe lipid granules C2 and the main leucocyte cluster B2, as shown in anenlarged view on the right side of FIG. 18. Therefore, the overlapbetween the lipid granules and the leucocyte cluster is avoided in thenew scatter diagram, so that the leucocyte particles and the lipidgranules can be distinguished from each other more easily and moreaccurately, thus facilitating the sorting.

In one embodiment, it is also possible not to determine whether or notthere is an overlap region according to an initial scatter diagram, andinstead, block 75 is performed directly after block 71.

In block 76, after selecting the forward-scattered light as a combinedoptical signal, the intensity of the forward-scattered light signal mayalso be multiplied by the forward-scattered pulse width to the power ofN (N is greater than 1) to obtain a forward-scatteredlight—forward-scattered pulse width reinforcement signal, for example,multiplying the intensity of the forward-scattered light signal by thesquare of the forward-scattered pulse width to obtain a reinforcementsignal. A new scatter diagram is formed by the side-scattered light andthe reinforcement signal. As shown in FIG. 19, the lipid granules C2 areshifted more to the lower right side relative to the main leucocytecluster B2, such that there is already an apparent empty space W betweenthe lipid granules C2 and the main leucocyte cluster B2, as shown in anenlarged view on the right side of FIG. 19. Therefore, the leucocyteparticles and the lipid granules can also be distinguished from eachother more easily and more accurately according to the new scatterdiagram.

In other embodiments, the abscissa and the ordinate of the new scatterdiagram may be different reinforcement signals. For example, theabscissa is a side-scattered—forward-scattered pulse width reinforcementsignal, and the ordinate is a forward-scattered—forward-scattered pulsewidth reinforcement signal.

In a further embodiment, the pulse width may also be the pulse width ofthe side-scattered light. In block 76, the forward-scattered light mayalso be selected as a combined optical signal, and the reinforcementsignal is a product of a forward-scattered light increasing function anda side-scattered pulse width increasing function, for example,multiplying the signal intensity of the forward-scattered light by theside-scattered pulse width to obtain a forward-scattered—side-scatteredpulse width reinforcement signal. In block 77, the side-scatteredfluorescence and the forward-scattered—side-scattered pulse widthreinforcement signal are selected to form a new scatter diagram, wherethe main leucocyte cluster is shifted more to the upper left siderelative to the lipid granules, such that the leucocyte particles andthe lipid granules can also be distinguished from each other.

According to the above disclosure, it is to be understood by thoseskilled in the art that the reinforcement signal may be a function ofthe combined optical signal and the pulse width in order to obtain ascatter diagram that can distinguish between the leucocyte particles andthe interfering particles, so long as the function increases thedifference in the reinforcement signal between the leucocyte particlesand the interfering particles relative to the difference between the twoin the combined optical signal.

The above embodiments illustrate the distinguishing between leucocytesand lipid granules or aggregated PLT particles. According to thedisclosed in the present application, it is to be understood by thoseskilled in the art that for two different categories of particles, ifthey differ in size in the overlap region, i.e., there are a differencein the pulse width between the two categories of particles in theoverlap region, the above embodiments can also be used to distinguishbetween the two categories of particles, for example, a routine test forfive types of leucocytes in certain scenes. When there is an overlapregion between two categories of particles, such as lymphocytes and amonocyte cluster having an overlap region, according to different pulsewidths of the particles of the lymphocytes and the monocyte cluster inthe overlap region, a new reinforcement signal can also be formed usingfunctions of an optical signal and a pulse width signal, and thelymphocytes and monocytes can be distinguished from each other based ona scatter diagram generated by the reinforcement signal, therebyobtaining a more accurate result of the five types.

The foregoing embodiments are described by taking the NRBC and BASOchannels commonly used in cell analyzers as examples. Those skilled inthe art will appreciate that in a leucocyte classification channel (DIFFchannel), it is also possible to distinguish between two categories ofoverlapping particles by using the method described above. Specifically,in the blood sample treated with the reagent, red blood cells aredissolved, each of cell particles in the sample liquid emits scatteredlights after being irradiated by the light beam, and forward-scatteredlights, side-scattered light, and/or medium-angle-scattered light signalare collected. Based on at least two types of scattered lights,leucocytes can be classified into four types of particles, i.e.,lymphocytes, monocytes, neutrophils, eosinophils, namely the leucocytefour classification (DIFF). It will be appreciated that leucocytes andaggregated platelet particles or lipid particles can be distinguishedfrom each other by a new scatter diagram including the reinforcementsignal acquired by using the foregoing methods. In another case, in theblood sample treated with the reagent, the red blood cells aredissolved, the cells are stained with a fluorescent dye, and theparticles in the sample liquid are irradiated by the light beam, suchthat fluorescent signals, forward scattered light, and/or side scatteredlight are collected. Based at least on fluorescent signals andside-scattered light signals, leucocytes can also be classified intofour types of particles, i.e., lymphocytes, monocytes, neutrophils, andeosinophils. Also, leucocyte particles and aggregated platelet particlesor lipid particles can be distinguished by a new scatter diagramincluding the reinforcement signal acquired by using the foregoingmethod.

In the foregoing embodiments, the reinforcement signal is calculatedbased on a product or a quotient between the combined signal and thepulse width signal. In other embodiments, instead of the product, thereinforcement signal is calculated based on a monotonic increasingfunction of the combined optical signal and a monotonic increasingfunction of the pulse width signal, or, the reinforcement signal iscalculated based on a monotonic decreasing function of the combinedoptical signal and a monotonic decreasing function of the pulse widthsignal; or, instead of the quotient, the reinforcement signal iscalculated based on a monotonic increasing function of one of thecombined optical signal and the pulse width signal and a monotonicdecreasing function of the other one.

It is to be understood by those skilled in the art that all or some ofthe blocks of the various cell analyzers in the embodiments describedabove could be achieved by special purpose hardware or by a generalpurpose processor executing instructions stored in a computer-readablestorage medium. The storage medium may include a read-only memory, arandom access memory, a magnetic disk, or an optical disk, or the like.

In addition, at least some of the function units in the above embodimentof the application may be integrated into a processor. When beingrealized in form of software function unit and sold or used as anindependent product, the function may also be stored in acomputer-readable storage medium. Based on such an understanding, thetechnical solutions of the application substantially or parts makingcontributions to the conventional art or part of the technical solutionsmay be embodied in form of software product, and the computer softwareproduct is stored in a storage medium, including a plurality ofinstructions configured to enable a processor (which may be the dataprocessing apparatus in the cell analyzer, or may be in a computerconnected to the cell analyzer) to execute all or part of the operationsof the method in each embodiment of the application. The abovementionedstorage medium includes: various media capable of storing program codessuch as a U disk, a mobile hard disk, a Read-Only Memory (ROM), a RandomAccess Memory (RAM), a magnetic disk or an optical disk.

The present disclosure has been set forth with reference to specificexamples, which are merely for the purpose of facilitating theunderstanding of the present disclosure and are not intended to limitthe same. It will be apparent to those of ordinary skill in the art thatchanges may be made to the specific embodiments described above inaccordance with the teachings of the present disclosure.

What is claimed is:
 1. A cell analyzer, comprising: a reaction chamber,that provides a location for reaction between a blood sample and areagent to get a sample liquid; a flow chamber having a detectionregion, through which the sample liquid pass in sequence with shroudingby a sheath liquid; a conveying apparatus having a conveying line and acontrol valve, wherein the sample liquid is conveyed into the flowchamber through the conveying line; an optical detection apparatushaving a plurality of optical signal detectors, operable to collectmultiple optical signals generated by each of particles irradiated withlight in a blood sample in a detection region, the particles comprisinga first category of particles and a second category of particles; and adata processing apparatus, configured to: for each of the particles,acquire intensities of a first group of optical signals, which compriseat least two optical signals selected from the multiple optical signals,and a pulse width of a second group of optical signals, which comprisesat least one optical signal selected from the multiple optical signals;for each of the particles, calculate one or more reinforcement signalsrelated to the particle, each reinforcement signal comprising areinforcement signal based on an intensity of a first optical signalselected from the first group of optical signals and a pulse width of asecond optical signal selected from the second group of optical signals,wherein the first optical signal is as same as or different from thesecond optical signal; and distinguish between the first category ofparticles and the second category of particles based at least partiallyon the one or more reinforcement signals related to each of theparticles.
 2. The cell analyzer of claim 1, wherein the data processingapparatus is configured to: generate a first scatter diagram for theparticles, based on the one or more reinforcement signals and anintensity of at least one optical signal, other than the first opticalsignal associated with any of the one or more reinforcement signals,selected from the first group of optical signals; and distinguishbetween the first category of particles and the second category ofparticles based on the first scatter diagram.
 3. The cell analyzer ofclaim 1, wherein the plurality of optical signal detectors comprise atleast two scattered light detectors selected from a forward-scatteredlight detector for collecting a forward-scattered light signal, aside-scattered light detector for collecting a side-scattered lightsignal, and a medium-angle-scattered light detector for collecting amedium-angle-scattered light signal, and wherein each of the firstoptical signal and the second optical signal is selected from theforward-scattered light signal, the side-scattered light signal, and themedium-angle-scattered light signal independently.
 4. The cell analyzerof claim 3, wherein at least one of the first optical signal or thesecond optical signal is the forward-scattered light signal.
 5. The cellanalyzer of claim 3, wherein the data processing apparatus is configuredto calculate the reinforcement signal based on an intensity of theforward-scattered light signal as the first optical signal and a pulsewidth of the forward-scattered light signal as the second opticalsignal.
 6. The cell analyzer of claim 5, wherein the first category ofparticles are leucocyte particles, and the second category of particlesare lipid granules or blood platelet (PLT) particles, wherein the dataprocessing apparatus is configured to distinguish between the firstcategory of particles and the second category of particles based on thereinforcement signal related to each of the particles and the intensityof the side-scattered light signal of the respective particle.
 7. Thecell analyzer of claim 3, wherein the plurality of optical signaldetectors comprise a front-scattered light detector for collecting afront-scattered light signal, and at least one of a side-scattered lightdetector for collecting a side-scattered light signal or amedium-scattered light detector for collecting a medium-scattered lightsignal, and wherein the data processing apparatus is further configuredto: distinguish leucocyte particles into lymphocytes, monocytes,neutrophil granulocytes and eosinophil granulocytes based on theforward-scattered light signal and the side-scattered light signal ofeach of the particles; or distinguish leucocyte particles intolymphocytes, monocytes, neutrophil granulocytes and eosinophilgranulocytes based on the forward-scattered light signal and themedium-angle-scattered light signal of each of the particles.
 8. Thecell analyzer of claim 1, wherein the plurality of optical signaldetectors comprise a fluorescence detector for collecting a fluorescencesignal and at least one scattered light detector for collecting arespective scattered light signal, and wherein the data processingapparatus is further configured to calculate the reinforcement signalbased on the fluorescence signal and at least one of the scattered lightsignal.
 9. The cell analyzer of claim 8, wherein the first category ofparticles are leucocyte particles, and the second category of particlesare aggregated platelet (PLT) particles.
 10. The cell analyzer of claim8, wherein the at least one scattered signal comprises aforward-scattered light signal and a side-scattered light signal, andwherein distinguishing between the first category of particles and thesecond category of particles comprises: generating a first scatterdiagram at least based on the reinforcement signal and a third opticalsignal selected from the first group of optical signals; anddistinguishing between the first category of particles and the secondcategory of particles based on the first scatter diagram, wherein eachof the first optical signal, the second optical signal, and the thirdoptical signal is different from one another, or each of the firstoptical signal, the second optical signal, and the third optical signalis selected from the fluorescence signal and the forward-scattered lightsignal.
 11. The cell analyzer of claim 1, wherein the plurality ofoptical signal detectors comprise a fluorescence detector for collectinga fluorescence signal, and a forward-scattered light detector forcollecting a forward-scattered light signal; and wherein the dataprocessing apparatus is further configured to: generate a second scatterdiagram based on the fluorescence signal and the forward-scattered lightsignal of each of the particles; and count nucleated red blood cellsbased on the second scatter diagram.
 12. The cell analyzer of claim 1,wherein the plurality of optical signal detectors comprise afluorescence detector for collecting a fluorescence signal, and aside-scattered light detector for collecting a side-scattered lightsignal; and wherein the data processing apparatus is further configuredto: distinguish leucocyte particles into lymphocytes, monocytes,neutrophil granulocytes and eosinophil granulocytes, based on thefluorescence signal and the side-scattered light signal of each of theparticles.
 13. The cell analyzer of claim 1, after acquiring theintensities of the first group of optical signals, the data processingapparatus is further configured to generate a third scatter diagrambased on the intensities of the first group of optical signals of eachof the particles; and wherein for each of the particles, data processingapparatus acquires the pulse width of the second group of opticalsignals when there is an overlap region of a cluster of the firstcategory of particles and a cluster of the second category of particlesin the third scatter diagram, to calculate the one or more reinforcementsignals.
 14. The cell analyzer of claim 1, wherein the reagent containsa hemolytic agent, and red blood cells are dissolved into blood ghostparticles.
 15. The cell analyzer of claim 1, wherein the reinforcementsignal is a non-linear combination function of the intensity of thefirst optical signal and the pulse width of the second optical signal,or the reinforcement signal is a monotonic function of the intensity ofthe first optical signal and the pulse width of the second opticalsignal.
 16. The cell analyzer of claim 1, wherein when Δs*Δw is greaterthan zero, the reinforcement signal is a monotonic increasing functionor a monotonic decreasing function of the intensity of the first opticalsignal and the pulse width of the second optical signal; or when Δs*Δwis less than zero, the reinforcement signal is a monotonic increasingfunction of the intensity of the first optical signal and a monotonicdecreasing function of the pulse width of the second optical signal, orthe reinforcement signal is a monotonic decreasing function of theintensity of the first optical signal and a monotonic increasingfunction of the pulse width of the second optical signal, wherein Δsrepresents a difference between a statistical intensity of the firstoptical signals of the first category of particles and that of the firstoptical signals of the second category of particles, and Δw represents adifference between a statistical pulse width of the second opticalsignals of the first category of particles and that of the secondoptical signals of the second category of particles.
 17. The cellanalyzer of claim 1, further comprising: a light source, operable toradiate the blood sample in the detection region with light; and aphotoelectric sensor, operable to convert the collected optical signalsto electric signals and output the electric signals to the dataprocessing apparatus.
 18. A non-transitory computer readable storagemedium, in which instructions are stored, wherein the instructions, whenexecuted by a processor, cause the processor to execute a method,comprising: collecting multiple optical signals generated by each ofparticles irradiated with light in a blood sample in a detection region,the particles comprising a first category of particles and a secondcategory of particles; for each of the particles, acquiring intensitiesof a first group of optical signals, which comprise at least two opticalsignals selected from the multiple optical signals, and a pulse width ofa second group of optical signals, which comprises at least one opticalsignal selected from the multiple optical signals; for each of theparticles, calculating one or more reinforcement signals related to theparticle, based on an intensity of a first optical signal selected fromthe first group of optical signals and a pulse width of a second opticalsignal selected from the second group of optical signals, wherein thefirst optical signal is as same as or different from the second opticalsignal; and distinguishing between the first category of particles andthe second category of particles based at least partially on the one ormore reinforcement signals related to each of the particles.